Proximal locking assembly design for dual stent mechanical thrombectomy device

ABSTRACT

A mechanical locking assembly for an endovascular device, comprising a shaft comprising a main body a shaft comprising a main body and enlarged end, an inner channel component comprising a full collar formed on proximal end of the inner channel component, and an outer cage component comprising a partial collar formed on the outer cage component wherein the full collar of the inner channel component fully surrounds the outer cage component and the partial collar of the outer cage component at least partially surrounds the shaft.

FIELD OF DISCLOSURE

The present disclosure generally relates to endovascular devices and methods, and, more particularly, to forming a proximal mechanical locking assembly on a dual stent mechanical thrombectomy device. This disclosure similarly relates to endovascular joint assemblies which can be used as components of endovascular devices used to remove blood vessel obstructions.

BACKGROUND

Recent clinical studies have shown that mechanical thrombectomy is an increasingly effective method of acute obstruction removal from blood vessels. Acute obstructions can include clots, misplaced devices, migrated devices, large emboli and the like. An ischemic stroke can result if an obstruction lodges in the cerebral vasculature. A pulmonary embolism can result if the obstruction, such as a clot, originates in the venous system or in the right side of the heart and lodges in a pulmonary artery or branch thereof. Mechanical thrombectomy typically involves advancing a thrombectomy device or stentriever to the occlusive clot, engaging with the clot and retracting the clot into the safety of a proximally placed guide or sheath.

However, despite the benefits provided by mechanical thrombectomy devices, there are limitations. For example, there are a number of procedural challenges that can place undue tension or compression on the device components. In cases where access involves navigating the aortic arch (such as coronary or cerebral blockages) the configuration of the arch in some patients makes it difficult to position a stentriever. These difficult arch configurations are classified as either type 2 or type 3 aortic arches with type 3 arches presenting the most difficulty. The tortuosity challenge is even more severe in the arteries approaching the brain. For example, it is not unusual at the distal end of the internal carotid artery that the device will have to navigate a vessel segment with a 180° bend, a 90° bend and a 360° bend in quick succession over a few centimeters of vessel. Delivering the device through the tortuous anatomy to the target location can apply compressive loading on the device components and joint between the distal section and the shaft. Moreover, dislodgement force of the obstruction in the vessel and retrieval through the tortuosity of the vasculature can place high tensile loading on the joint. Retrieval of the obstruction into the access catheter can also place high forces on the device components and proximal joint to the shaft.

These endovascular devices can be integrally formed with joint assemblies, often connecting a clot engaging portion to an elongated shaft. These assemblies can rely on adhesive bonds, weld bonds, or soldering. Adhesive can be applied to ensure the components maintain the correct position and orientation but increased joint strength and integrity can be desirable in some instances.

Moreover, as shown in FIG. 1, current proximal mechanical bonds on dual stent mechanical thrombectomy devices generally include a stepped nitinol shaft 10, an outer cage component 30 with full cylindrical proximal collar 32, and an inner channel component 20 with partial C-collar. The three components are assembled such that a mechanical lock is formed so that the components cannot separate under tension without material deformation or failure. However, in order to maintain the appropriate crossing profile (and maintain 0.021″ or 0.017″ microcatheter compatibility) the design of the outer cage collar component requires that the nitinol tubing raw material used to form this component has a maximum outer diameter that is smaller than the microcatheter inner diameter. Forming a similar proximal mechanical lock is problematic if a larger diameter nitinol tubing raw material is specified for the outer cage component.

There therefore exists a need for an endovascular device with a proximal joint compatible with varying sizes of raw material tubing that has sufficient integrity for effectively capturing an obstruction for safe retrieval from a patient.

SUMMARY

Disclosed herein are various exemplary endovascular devices of the present disclosure that can address the above needs. The devices can be joint assemblies that generally can include a shaft, an outer cage component including an outer cage collar and an outer cage proximal strut, and an inner channel component including an inner channel collar and an inner channel proximal strut. The joint assemblies can be integrally joined to an endovascular device, between a clot engaging portion and an elongated shaft. In this manner, the joint assemblies permit for an obstruction to be captured by the clot engaging portion of an endovascular device with increased load support provided by the joint assemblies. In another example, a joint assembly of a dual stent thrombectomy device having an inner channel component and an outer cage component including a proximal mechanical lock, having a shaft comprising a main body and enlarged end, a full collar formed on the inner channel component, and a partial collar formed on the outer cage component. The partial collar of the outer cage component can at least partially surround the shaft and the full collar of the inner channel component can fully surround the partial collar of the outer cage component.

In another example, a joint assembly includes a joint assembly for an endovascular device, having a shaft comprising a main body and an enlarged end, a proximal strut comprising a strut slot and at least one strut slit, and a locking collar having a distal face and at least one collar pin protruding from the locking collar near the distal face of the collar, wherein the strut slot engages the enlarged end of the shaft, and wherein the proximal strut is configured to permit the strut slit to flex to lockingly engage the at least one collar pin.

In one example, the joint assembly for an endovascular device can include a shaft having a main body and an enlarged end, a locking collar, a first proximal strut including a first slot, and a second proximal strut including a second slot, wherein each of the first and second slots engage the enlarged end of the shaft, and wherein the locking collar at least partially covers the enlarged end of the shaft and the first and second slots of the first and second proximal struts. In some embodiments, at least a portion of the enlarged end is received in both of the proximal strut slots. In some embodiments, the enlarged end of the shaft defines a shaft step with the main body of the shaft. In some embodiments, the locking collar constrains the first proximal strut and the second proximal strut such that the first strut slot and the second strut slot cannot disengage from the enlarged end of the shaft when the joint assembly is under compressive or tensile load.

BRIEF DESCRIPTION OF THE DRAWINGS

The above and further aspects of this disclosure are further discussed with reference to the following description in conjunction with the accompanying drawings, in which like numerals indicate like structural elements and features in various figures. The drawings are not necessarily to scale, emphasis instead being placed upon illustrating principles of the disclosure. The figures depict one or more implementations of the inventive devices, by way of example only, not by way of limitation.

FIG. 1 illustrates a configuration of an exemplary prior art mechanical locking assembly;

FIG. 2 illustrates a perspective view of an exemplary mechanical locking assembly of the present disclosure;

FIG. 3 illustrates a configuration of an exemplary prior art joint assembly;

FIG. 4 illustrates a configuration of an exemplary joint assembly of the present disclosure;

FIG. 5 illustrates a side view of a locking collar in accordance with an exemplary joint assembly of the present disclosure;

FIG. 6 illustrates a configuration of an exemplary joint assembly of the present disclosure;

FIG. 7 illustrates an alternative configuration of an exemplary joint assembly of the present disclosure;

FIG. 8 illustrates a side view of an exemplary joint assembly of the present disclosure;

FIG. 9 illustrates a top view of an exemplary joint assembly of the present disclosure;

FIG. 10 illustrates a side view of a locking collar in accordance with an exemplary joint assembly of the present disclosure; and

FIG. 11 illustrates a side view of an alternate configuration of an exemplary joint assembly of the present disclosure.

DETAILED DESCRIPTION

Specific embodiments of the present disclosure are now described in detail with reference to the figures, wherein identical reference numbers indicate identical or functionality similar elements. The terms “distal” or “proximal” are used in the following description with respect to a position or direction relative to the treating physician. “Distal” or “distally” are a position distant from or in a direction away from the physician. “Proximal” or “proximally” or “proximate” are a position near or in a direction toward the physician.

As used herein, the terms “about” or “approximately” for any numerical values or ranges indicate a suitable dimensional tolerance that allows the part or collection of components to function for its intended purpose as described herein. More specifically, “about” or “approximately” may refer to the range of values ±20% of the recited value, e.g. “about 90%” may refer to the range of values from 71% to 99%

Accessing cerebral, coronary and pulmonary vessels involves the use of a number of commercially available products and conventional procedural steps. Access products such as stentrievers and thrombectomy devices are described elsewhere and are regularly used in endovascular procedures. See, for example U.S. Patent Publication 2015/0164523 which is hereby incorporated by reference in its entirety herein as if set forth in full. It is assumed in the descriptions below that these products and methods are employed in conjunction with the device and methods of this disclosure and do not need to be described in detail.

The following detailed description is merely exemplary in nature and is not intended to limit the disclosure or the application and uses of the disclosure. Although the description of the disclosure is in many cases in the context of treatment of blood vessel occlusions, the disclosure may also be used in other body passageways as described herein.

An example of a joint assembly, as illustrated in FIG. 2, can have a shaft 100, an inner channel component 118 comprising a full collar 122 formed on proximal end of the inner channel component 118, and an outer cage component 130 comprising a partial collar 132 formed on the outer cage component 130. The shaft 100 can include a main body 110 and enlarged end 112. In some embodiments, the full collar 122 of the inner channel component 118 can fully surround the partial collar 132 of the outer cage component 130. The partial collar 132 of the outer cage component 130 can at least partially surround the shaft 100. In some examples, the partial collar 132 of the outer cage component 130 can be C-shaped in cross section over at least a portion of its length such that the partial collar only partially surrounds the shaft in the portion of the partial collar 132 having the C-shaped cross section. In some examples, the outer cage component and the inner channel component can each respectively include an integrally joined proximal strut. The diameter of the collar 122 of the inner channel component 118 can range from about 0.021 inches to about 2 inches (e.g. 0.025 inches, 0.030 inches, 0.075 inches, 0.15 inches, 0.45 inches, 0.1 inches, 0.5 inches, 0.8 inches, 1.5 inches, 1.75 inches). Similarly, the diameter of the collar 132 of the outer cage component 130 can range from about 0.001 inches to about 0.021 inches (e.g. 0.019 inches, 0.017 inches, 0.015 inches, 0.013 inches, 0.011 inches, 0.009 inches, 0.007 inches, 0.005 inches, 0.003 inches, 0.001 inches). The diameter of the collar 132 of the outer cage component 130 can be measured based on the outer perimeter of a circle including the arc of the C-shaped collar 132.

As shown in FIG. 3, a previously disclosed joint assembly can include a shaft 40 including a main body 42 and an enlarged step 44, a proximal strut 48 engaging with shaft 40, and a locking collar 46 engagingly receiving at least a portion of main body 42 and at least a portion of proximal strut 48 to lock the assembly into place. It may further include a proximal strut slot 49. Undue tension can elicit sufficient tensile stress on the shaft to cause the proximal strut to disengage from the enlarged step of the shaft, thereby causing the enlarged end to deform. This can result in disassembly of the joint device of the stentriever or thrombectomy device during dislodgement of the obstruction or as it is withdrawn proximally around a bend in a tortuous vessel, or the potential escape of the captured clot.

FIGS. 4-5 show an alternative joint assembly embodiment in accordance with this disclosure. This joint assembly can include a shaft 200 with a main body 210 and an enlarged end 212. In this embodiment, inner channel collar 230 and the inner channel component such as proximal strut 218 are integrally joined to each other and the inner channel collar 230 is attached to the outer cage proximal strut 220 by any suitable means. The outer cage proximal strut 220 can be distal of the shaft 200 and at the proximal end of the stentriever. The inner channel collar 230 can have the same diameter as the raw material tubing from which it is cut. This removes the need for separate outer cage and inner channel components to achieve the mechanical lock between components in the assembly. In some embodiments, the outer cage proximal strut 220 can engage the inner channel collar 230 such that the inner channel collar 230, shaft 200, and outer cage proximal strut 220 are lockingly engaged by friction-fit. The friction-fit engagement can prevent the outer cage proximal strut 220 from disengaging from the enlarged end 212 of the shaft 200 when the joint assembly is integrally formed into an endovascular device and the endovascular device is under load.

The proximal strut 220 of the outer cage 220 can further include a strut slot 222 having an opening in which a portion of the enlarged end 212 of the shaft 200 can be positioned. When the enlarged end 212 of the shaft 200 is positioned in the slot 222 of the proximal strut 220 of the outer cage, the inner channel collar 230 can be positioned to at least partially surround the enlarged end 212 of the shaft 200 and the slot 222 of the proximal strut 220 of the outer cage to effectively secure the enlarged end 212 within the slot 222.

As shown in FIG. 6, an exemplary joint assembly can include a shaft 300, a first proximal strut 320, a locking collar 330, and a second proximal strut 340. The first and second proximal struts 320, 340 are distal of the shaft 300 but at the proximal end of the stentriever. In some embodiments, the shaft 300 can include a main body 310 and an enlarged end 312. The enlarged end 312 can include a top end 314 and a bottom end 316. In some embodiments, the first proximal strut 320 can include a first strut slot 322. In some embodiments, the second proximal strut 340 can include a second strut slot 342. In some embodiments, the first slot 322 can engage the top end 314 of the enlarged end 112 of the shaft 100. As shown in FIG. 7, the second slot 342 can engage the bottom end 316 of the enlarged end 312 of the shaft 300. In some embodiments, the locking collar 330 can at least partially cover the enlarged end 312 of the shaft 300, first slot 322 of the first proximal strut 320, and second strut slot 342 of the second proximal strut 340. In some embodiments, at least a portion of the enlarged end 112 is received in the first proximal strut slot 322, the second strut slot 342 of the second proximal strut 340, or both the first slot 322 and the second slot 342. In some embodiments, the enlarged end 312 of the shaft 300 defines a shaft step 313 with the main body 310 of the shaft 300. In some embodiments, the proximal strut further includes a tail 324.

As shown in FIG. 8, in some embodiments, an exemplary joint assembly can include a shaft 400, a proximal strut 420, and a locking collar 430. The proximal strut 420 is distal of the shaft 400 but at the proximal end of the stentriever. In some embodiments, the shaft 400 can include a main body 410 and an enlarged end 412. In some embodiments, the proximal strut 420 can include slot 422 and/or strut slits 424, as shown in FIG. 9. In some embodiments, the slot 422 can engage the enlarged end 412 of the shaft 400. As shown in FIG. 10, locking collar 430 can include a distal face 434 and collar pins 432 near the distal face of locking collar 430. FIG. 11 shows that the collar pins 432 can lock into strut slits 424 of the proximal strut 420 when the shaft 400 is pulled inside the locking collar 430, forming a mechanical lock. Proximal strut 420 can include a flexible material such that its flexes to permit strut slits 424 to engage collar pins 432. In this proposed design the collar will be locked in place, this mechanical lock will add extra tensile strength for advancement and retrieval, the use of UV glue may no longer be mandatory. During assembly, the operator need only place the proximal strut 420 over the enlarged end 412 of the shaft 400 and pull both through the locking collar 430, and the flexible nitinol strut will lock in place on the collar pins 432. The locking collar 430 constrains the proximal strut slot 422 relative to enlarged end 412 such that proximal strut slot 422 maintains engagement with enlarged end 412 under tensile load up to a force of from about 2N to 15N (e.g. 3N, 4N, 5N, 6N, 7N, 8N, 9N, 10N, 11N, 12N, 13N, 14N).

In some embodiments, the joint assembly can be any suitable size and shape to be compatible with microcatheters used for neurovascular device delivery. The proximal strut slot can be any suitable shape for engaging enlarged end. For example, suitable shapes for the proximal strut slot can include generally square, generally rectangular, generally circular, and the like. Both the inner channel component and the outer cage component can be any suitable shape for covering or enclosing at least a portion of the proximal strut slot and the enlarged end of shaft. Suitable shapes for outer cage component can include generally partially cylindrical, generally partially elliptical cylindrical, and the like. Suitable shapes for inner channel component can include generally cylindrical, generally elliptical cylindrical, and the like. Main body and enlarged end of shaft can be any suitable size and shape for engaging proximal strut and being received, at least partially, in the inner channel component and the outer cage component. Suitable shapes for main body can include generally cylindrical, generally elliptical cylindrical, and the like. Suitable shapes for enlarged end can include generally cylindrical, generally elliptical cylindrical, and the like. In some embodiments, the joint assembly can be sized to be compatible with microcatheters with an inner diameter of 0.027 inches or less (e.g. 0.026 inches, 0.024 inches, 0.022 inches, 0.019 inches, 0.017 inches, 0.015 inches, 0.013 inches, 0.011 inches, 0.009 inches, 0.007 inches, 0.005 inches, 0.003 inches, 0.001 inches), and preferably with a microcatheter having an inner diameter of 0.021 inches or less (e.g. 0.019 inches, 0.017 inches, 0.015 inches, 0.013 inches, 0.011 inches, 0.009 inches, 0.007 inches, 0.005 inches, 0.003 inches, 0.001 inches).

Suitable materials for forming the shaft, proximal strut, and collar ideally have a high tensile strength such that sufficient integrity for manufacturability and use can be produced, such as for example polymers materials like UHMWPE, Aramid, LCP, PET or PEN, or metals such as Tungsten, MP35N, stainless steel or Nitinol. The proximal strut slot can be any suitable shape for engaging the enlarged end.

In some embodiments, any of the above-described joint assemblies can be integrally joined to an endovascular device between a clot engaging portion and an elongated shaft. Examples of endovascular devices can include a stentriever, thrombectomy device, coil retriever, equivalents thereof now known or later discovered, or combinations thereof.

The descriptions contained herein are examples of embodiments of the disclosure and are not intended in any way to limit the scope of the disclosure. As described herein, the disclosure contemplates many variations and modifications of the joint assemblies, including varied positioning of the shaft, proximal strut, and collar, utilizing any of numerous materials for each element or member, incorporation of additional elements or members, for example. These modifications would be apparent to those having ordinary skill in the art to which this disclosure relates and are intended to be within the scope of the claims which follow. 

1. A proximal mechanical locking assembly for a thrombectomy device, comprising: a shaft comprising a main body and enlarged end; an inner channel component comprising a full collar formed on a proximal end of the inner channel component; and an outer cage component comprising a partial collar formed on the outer cage component, wherein the partial collar of the outer cage component at least partially surrounds the shaft and the full collar of the inner channel component fully surrounds the partial collar of the outer cage component.
 2. The proximal mechanical locking assembly of claim 1, wherein the enlarged end of the shaft defines a shaft step with the main body of the shaft.
 3. The proximal mechanical locking assembly of claim 1, wherein the full collar of the inner channel component is generally cylindrical.
 4. The proximal mechanical locking assembly of claim 1, wherein the partial collar of the outer cage component is C-shaped.
 5. The proximal mechanical locking assembly of claim 1, wherein the diameter of the outer cage component is from about 0.021 inches to about 2 inches.
 6. The proximal mechanical locking assembly of claim 1, wherein the diameter of the inner channel component is from about 0.001 inches to about 0.021 inches.
 7. A method of forming a proximal mechanical locking assembly for a thrombectomy device, comprising: providing a shaft comprising a main body, an inner channel component comprising a full collar formed on the proximal end of the inner channel component, and an outer cage component comprising a partial collar formed on the outer cage component; positioning the outer cage component at least partially around the shaft and positioning the inner channel component at least partially around the outer cage component, such that the shaft, inner channel component, and outer cage component are mechanically locked.
 8. The method of claim 7, wherein the shaft further comprises an enlarged end.
 9. The method of claim 7, wherein the enlarged end of the shaft defines a shaft step with the main body of the shaft.
 10. The method of claim 9, wherein the full collar of the inner channel component is generally cylindrical.
 11. The method of claim 7, wherein the partial collar of the outer cage component is C-shaped.
 12. The method of claim 7, wherein the diameter of the outer cage component is from about 0.021 inches to about 2 inches.
 13. The method of claim 7, wherein the diameter of the inner channel component is from about 0.001 to about 0.021 inches.
 14. A proximal mechanical locking assembly for a thrombectomy device, comprising: a shaft comprising a main body and enlarged end; an inner channel component comprising a proximal collar; and an outer cage component comprising a proximal strut the proximal strut comprising a slot opening therethrough, wherein the enlarged end is positioned within the slot opening of the outer cage component and the proximal collar of the inner channel component at least partially surrounds the enlarged end and the slot opening.
 15. The proximal mechanical locking assembly of claim 14, wherein the inner channel component is curved.
 16. A joint assembly for an endovascular device, comprising: a shaft comprising a main body and an enlarged end, the enlarged end having a top end and a bottom end; a first proximal strut comprising a first slot, wherein the first slot engages the top end of the enlarged end of the shaft; a second proximal strut comprising a second slot, wherein the second slot engages the bottom end of the enlarged end of the shaft; and a locking collar at least partially covering the enlarged end of the shaft, the first slot of the first proximal strut, and the second slot of the second proximal strut.
 17. The joint assembly of claim 16, wherein at least a portion of the enlarged end is received in the both the first strut slot and the second strut slot.
 18. The joint assembly of claim 16, wherein the collar constrains the first proximal strut and the second proximal strut such that the first strut slot and the second strut slot cannot disengage from the enlarged end of the shaft when the joint assembly is loaded into a clot retrieval device and the clot retrieval device is under load.
 19. A joint assembly for an endovascular device, comprising: a shaft comprising a main body and an enlarged end; a proximal strut comprising a strut slot and at least one strut slit; and a locking collar having a distal face and at least one collar pin protruding from the locking collar near the distal face of the collar, wherein the strut slot engages the enlarged end of the shaft, and wherein the proximal strut is configured to flex to permit the strut slit to lockingly engage the at least one collar pin.
 20. The joint assembly of claim 19, wherein the proximal strut includes a flexible material. 